CN104267359A - Gradient coil used for magnetic resonance imaging - Google Patents
Gradient coil used for magnetic resonance imaging Download PDFInfo
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- CN104267359A CN104267359A CN201410556863.7A CN201410556863A CN104267359A CN 104267359 A CN104267359 A CN 104267359A CN 201410556863 A CN201410556863 A CN 201410556863A CN 104267359 A CN104267359 A CN 104267359A
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Abstract
The invention discloses a gradient coil used for magnetic resonance imaging. The gradient coil is characterized by comprising a first main coil and a second main coil; the first main coil and the second main coil each comprise a first coil Cx, a second coil Cy, a third coil Cz, an active shim coil Cs and insulating layers; each first coil Cx, the corresponding second coil Cy, the corresponding third coil Cz and the corresponding active shim coil Cs are sequentially arranged in the same vertical plane in parallel at intervals, the insulating layers are arranged between each first coil Cx and the corresponding second coil Cy, between each second coil Cy and the corresponding third coil Cz and between each third coil Cz and the corresponding active shim coil Cs; when the first main coil and the second main coil are installed on a magnet in a matched mode, the same coils in the first main coil and the second main coil are connected in series, the first coils Cx, the second coils Cy, the third coils Cz and the active shim coils Cs are all oval, and the first main coil and the second main coil are matched so that an oval imaging region can be acquired.
Description
Technical field
The present invention relates to a kind of gradient coil, particularly about a kind of for the gradient coil in magnetic resonance imaging.
Background technology
Magnetic resonance imaging (Magnetic Resonance Imaging, MRI) equipment is one of greatest invention in last century, almost can be used for the scanning at each position of human body, not have ionization radiation injury to human body, soft tissue structure's display is clear, can be used for each site disorders diagnosis of whole body.Gradient coil is the important ingredient of MRI equipment one, is mainly used to the linear gradient magnetic field in generation three directions, selects layer, phase encoding and frequency coding to MRI signal, for image reconstruction provides basis on location.The performance of development to gradient coil of MRI technology is had higher requirement, therefore to the design of gradient coil, structure is optimized is significantly.
As shown in Figure 1, because human body is similar to elongated cylinder structure, therefore when using body coil to carry out imaging to body and centrum, to the demand of Y direction areas imaging than X-direction and Z-direction larger.The imaging area of existing MRI system is designed to circle, although can meet the demand of areas imaging in Y-direction like this, some space is wasted in the X direction, adds manufacturing cost.
Summary of the invention
For the problems referred to above, the object of this invention is to provide and a kind ofly effectively can adapt to organization of human body feature, produce oval imaging region for the gradient coil in magnetic resonance imaging.
For achieving the above object, the present invention takes following technical scheme: a kind of for the gradient coil in magnetic resonance imaging, it is characterized in that: it comprises the first main coil and the second main coil, described first main coil and the second main coil include the first coil Cx, second coil Cy, tertiary coil Cz, active shimming coils Cs and insulation course, described first coil Cx, second coil Cy, tertiary coil Cz and active shimming coils Cs is spaced and parallel setting successively in same perpendicular, between described first coil Cx and the second coil Cy, between described second coil Cy and tertiary coil Cz and between described tertiary coil Cz and active shimming coils Cs, all insulation course is set, when described first main coil and the cooperation of the second main coil are arranged on magnet, described first coil Cx in described first main coil connects with the described first coil Cx in described second main coil, described second coil Cy in described first main coil connects with the described second coil Cy in described second main coil, described tertiary coil Cz in described first main coil connects with the described tertiary coil Cz in described second main coil, and the described active shimming coils Cs in described first main coil connects with the described active shimming coils Cs in described second main coil, the shape of described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs is all set to ellipse, described first coil Cx, the second coil Cy, tertiary coil Cz are respectively used to the gradient fields producing X-direction, Y-direction and Z-direction, and described first main coil and the second main coil coordinate the imaging region obtaining elliposoidal.
Described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs all adopt copper wire winding or copper coin to process, and a connection terminal is installed at the two ends of copper cash or copper coin respectively.
For described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs, the length Ly of each coil Y-direction is all greater than the length Lx of its X-direction.
For described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs, the ratio range of each length Ly of coil Y-direction and the length Lx of its X-direction is set to 1<L
y/ L
x≤ 1.3.
For described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs, the ratio of each length Ly of coil Y-direction and the length Lx of its X-direction is 1.14.
The present invention is owing to taking above technical scheme, it has the following advantages: 1, the present invention is owing to comprising the first and second main coils, first and second main coils include the first coil Cx, second coil Cy, tertiary coil Cz, active shimming coils Cs and insulation course, first coil Cx, second coil Cy, the shape of tertiary coil Cz and active shimming coils Cs is all set to ellipse, and the length Ly of each coil Y-direction is all greater than the length Lx of its X-direction, when first and second main coils cooperations are arranged in magnet, identical coils connected in series in first and second main coils, therefore the present invention can obtain the imaging region of elliposoidal, adapt to organization of human body feature, thus can effectively prevent the gradient signal outside imaging region to be applied into image formation compression artefacts.2, the present invention is owing to being set to 1<L by the ratio range of each length of coil Y-direction in the first and second main coils and the length Lx of its X-direction
y/ L
x≤ 1.3, therefore the present invention is while effectively meeting body scans demand, farthest can reduce manufacturing cost, and lays the foundation for the expansion of MR imaging apparatus range of application.Based on above advantage, the present invention can be widely used in magnetic resonance imaging system.
Accompanying drawing explanation
Fig. 1 is the view adopting magnetic resonance system scanning
Fig. 2 is the structural representation of gradient coil of the present invention
Fig. 3 is the positional structure schematic diagram of gradient coil of the present invention in magnet
Fig. 4 is the schematic shapes of each coil in gradient coil of the present invention
Fig. 5 is the stretching schematic diagram of the second coil Cy
Fig. 6 is the structural representation of the second coil Cy
Fig. 7 is the structural representation of the first coil Cx
Fig. 8 is the structural representation of tertiary coil Cz
Fig. 9 is the test result curve of the first coil Cx in embodiment
Figure 10 is the test result curve of the second coil Cy in embodiment
Figure 11 is the test result curve of tertiary coil Cz in embodiment
Embodiment
Below in conjunction with drawings and Examples, the present invention is described in detail.
As shown in Figure 2, the gradient coil that the present invention is used in magnetic resonance imaging comprises the first main coil 1 and the second main coil 2, wherein, first main coil 1 and the second main coil 2 include the first coil Cx, second coil Cy, tertiary coil Cz, active shimming coils Cs and insulation course, first coil Cx, second coil Cy, tertiary coil Cz and active shimming coils Cs is spaced and parallel setting successively in same perpendicular, between first coil Cx and the second coil Cy, between second coil Cy and tertiary coil Cz and tertiary coil Cz and active shimming coils Cs all insulation course is set.
As shown in Figures 2 and 3, the first main coil 1 and the cooperation of the second main coil 2 are arranged on magnet, obtain the imaging region of elliposoidal.First main coil 1 and the second main coil 2 with the use of time, the first coil Cx in first main coil 1 connects with the first coil Cx in the second main coil 2, the second coil Cy in first main coil 1 connects with the second coil Cy in the second main coil 2, tertiary coil Cz in first main coil 1 connects with the tertiary coil Cz in the second main coil 2, and the active shimming coils Cs in the first main coil 1 connects with the active shimming coils Cs in the second main coil 2.First coil Cx, the second coil Cy and tertiary coil Cz are respectively used to the gradient fields producing X-direction, Y-direction and Z-direction.
As shown in Figure 4, according to the feature of organization of human body, the shape of the first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs is all set to ellipse, the length Ly of each coil Y-direction is all greater than the length Lx of its X-direction, thus makes the equal ovalize of areas imaging that the first coil Cx, the second coil Cy and tertiary coil Cz are formed.
In above-described embodiment, the first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs all adopt copper wire winding or copper coin to process, and a connection terminal is installed at the two ends of copper cash or copper coin respectively.
In above-described embodiment, for the first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs, according to factors such as organization of human body, the structure of magnet coordinated with this gradient coil and the efficiency of gradient coil, based on practicality and economy, the ratio range of each length Ly of coil Y-direction and the length Lx of its X-direction is set to 1<L
y/ L
x≤ 1.3.
Embodiment: first, adopt Electric current density method design to obtain a traditional gradient coil, the length of its imaging region Y-direction equals the length of X-direction.Secondly, for the second coil Cy in the first main coil 1 and the second main coil 2, as shown in Figure 5, the length of the second coil Cy all stretched along its Y-direction, the ratio of the length Ly of this coil Y-direction and the length Lx of its X-direction is 1.14.Finally, utilize separated wires method to calculate the situation of change of the rear gradient fields of the second coil Cy stretching, the situation of change according to gradient fields is finely tuned the second coil Cy, obtains coil as shown in Figure 6.For the first coil Cx, tertiary coil Cz and active shimming coils Cs, the method identical with the second coil Cy is all adopted to process.Wherein, measure-alike all with the second coil Cy of the coil dimension of the first coil Cx, tertiary coil Cz and active shimming coils Cs.The length of coil Y-direction is 1018mm, and the length of X-direction is 890mm, and the length of Z-direction is 20mm.Between first coil Cx and the second coil Cy, between the second coil Cy and tertiary coil Cz and the insulation course of a 0.5mm is all set between tertiary coil Cz and active shimming coils Cs.
As shown in Figure 7, the number of turn of the first coil Cx is 40, and inductance is 954 μ H, resistance 157.85m Ω; As shown in Figure 6, the number of turn of the second coil Cy is 40, and inductance is 955 μ H, and resistance is 140.82m Ω; As shown in Figure 8, the number of turn of tertiary coil Cz is 36, and inductance is 595.4 μ H, and resistance is 77.43m Ω.The gradient coil that first main coil 1 and the second main coil 2 are formed is tested, in X-direction, the test result of magnetic induction density is as shown in Figure 9 when Y=0, Z=0 for first coil Cx, wherein transverse axis represents the distance of test point to the first coil Cx center, the magnetic induction density of test point when the longitudinal axis represents that the first coil Cx powers up; Second coil Cy when X=0, Z=0 in Y-direction the test result of magnetic induction density as shown in Figure 10, wherein transverse axis represents the distance of test point to the second coil Cy center, the magnetic induction density of test point when the longitudinal axis represents that the second coil Cy powers up; Tertiary coil Cz when X=0, Y=0 in Z-direction the test result of magnetic induction density as shown in figure 11, wherein transverse axis represents that test point arrives the distance at tertiary coil Cz center, the magnetic induction density of test point when the longitudinal axis represents that tertiary coil Cz powers up.The size of this gradient coil imaging region of size Expressing in the curve linear region of three shown in Fig. 9 ~ Figure 11.As can be seen from test result, range L x × Ly × the Lz of this gradient coil imaging region is greater than 400mm × 500mm × 320mm, therefore the indices of this gradient coil meets the requirements, and the areas imaging of Y-direction obviously expands, thus the gradient signal outside imaging region can be effectively prevented to be applied into image formation compression artefacts.
The various embodiments described above are only for illustration of the present invention; wherein the structure of each parts, connected mode and method step etc. all can change to some extent; every equivalents of carrying out on the basis of technical solution of the present invention and improvement, all should not get rid of outside protection scope of the present invention.
Claims (5)
1. one kind for the gradient coil in magnetic resonance imaging, it is characterized in that: it comprises the first main coil and the second main coil, described first main coil and the second main coil include the first coil Cx, second coil Cy, tertiary coil Cz, active shimming coils Cs and insulation course, described first coil Cx, second coil Cy, tertiary coil Cz and active shimming coils Cs is spaced and parallel setting successively in same perpendicular, between described first coil Cx and the second coil Cy, between described second coil Cy and tertiary coil Cz and between described tertiary coil Cz and active shimming coils Cs, all insulation course is set, when described first main coil and the cooperation of the second main coil are arranged on magnet, described first coil Cx in described first main coil connects with the described first coil Cx in described second main coil, described second coil Cy in described first main coil connects with the described second coil Cy in described second main coil, described tertiary coil Cz in described first main coil connects with the described tertiary coil Cz in described second main coil, and the described active shimming coils Cs in described first main coil connects with the described active shimming coils Cs in described second main coil, the shape of described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs is all set to ellipse, described first coil Cx, the second coil Cy, tertiary coil Cz are respectively used to the gradient fields producing X-direction, Y-direction and Z-direction, and described first main coil and the second main coil coordinate the imaging region obtaining elliposoidal.
2. a kind of for the gradient coil in magnetic resonance imaging as claimed in claim 1, it is characterized in that: described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs all adopt copper wire winding or copper coin to process, and a connection terminal is installed at the two ends of copper cash or copper coin respectively.
3. a kind of for the gradient coil in magnetic resonance imaging as claimed in claim 1 or 2, it is characterized in that: for described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs, the length Ly of each coil Y-direction is all greater than the length Lx of its X-direction.
4. a kind of for the gradient coil in magnetic resonance imaging as claimed in claim 3, it is characterized in that: for described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs, the ratio range of each length Ly of coil Y-direction and the length Lx of its X-direction is set to 1<L
yl
x≤ 1.3.
5. a kind of for the gradient coil in magnetic resonance imaging as claimed in claim 4, it is characterized in that: for described first coil Cx, the second coil Cy, tertiary coil Cz and active shimming coils Cs, the ratio of each length Ly of coil Y-direction and the length Lx of its X-direction is 1.14.
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| CN201410556863.7A CN104267359B (en) | 2014-10-20 | 2014-10-20 | A kind of gradient coil being used in magnetic resonance imaging |
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Cited By (4)
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| CN104730476A (en) * | 2015-02-28 | 2015-06-24 | 中国科学院电工研究所 | Planar gradient coil for magnetic resonance microimaging |
| CN105044635A (en) * | 2015-06-12 | 2015-11-11 | 北京斯派克科技发展有限公司 | Gradient coil for joint magnetic resonance imaging |
| CN109917312A (en) * | 2019-01-31 | 2019-06-21 | 佛山瑞加图医疗科技有限公司 | Magnetic resonance imaging gradient coil and its processing method |
| CN110412492A (en) * | 2018-04-27 | 2019-11-05 | 西门子医疗有限公司 | Gradient coil unit for magnetic resonance equipment |
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Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN104730476A (en) * | 2015-02-28 | 2015-06-24 | 中国科学院电工研究所 | Planar gradient coil for magnetic resonance microimaging |
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| CN110412492A (en) * | 2018-04-27 | 2019-11-05 | 西门子医疗有限公司 | Gradient coil unit for magnetic resonance equipment |
| CN110412492B (en) * | 2018-04-27 | 2022-03-25 | 西门子医疗有限公司 | Gradient coil unit for a magnetic resonance system |
| CN109917312A (en) * | 2019-01-31 | 2019-06-21 | 佛山瑞加图医疗科技有限公司 | Magnetic resonance imaging gradient coil and its processing method |
| CN109917312B (en) * | 2019-01-31 | 2021-09-21 | 佛山瑞加图医疗科技有限公司 | Gradient coil for magnetic resonance imaging and processing method thereof |
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| CN104267359B (en) | 2017-12-15 |
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